|Publication number||US7169174 B2|
|Application number||US 10/771,181|
|Publication date||Jan 30, 2007|
|Filing date||Feb 3, 2004|
|Priority date||Jun 30, 2000|
|Also published as||US6540775, US6706061, US20030100941, US20040204751, US20070239258|
|Publication number||10771181, 771181, US 7169174 B2, US 7169174B2, US-B2-7169174, US7169174 B2, US7169174B2|
|Inventors||Robert E. Fischell, David R. Fischell, Tim A. Fischell|
|Original Assignee||Cordis Corporation|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (101), Referenced by (60), Classifications (15), Legal Events (4)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a continuation of Ser. No. 09/718,558, filed Nov. 22, 2000, now U.S. Pat. No. 6,706,061, which is a continuation-in-part of Ser. No. 09/607,980, filed Jun. 30, 2000, now U.S. Pat. No. 6,540,775.
This invention is in the field of stents for implantation into a vessel of a human body.
Stents are well known medical devices that have been used for maintaining the patency of a large variety of vessels of the human body. The most frequent use is for implantation into the coronary vasculature. Although stents have been used for this purpose for more than ten years, many stent designs still lack the required flexibility and radial rigidity to provide an optimum clinical result. Another deficiency of open cell stents is that some stent struts members can flare outward (fish scaling) as the stent is advanced through a tight curve.
An open cell stent is defined as a stent that has circumferential sets of strut members with some curved sections (crowns) that are not connected by a longitudinal connecting link to an adjacent circumferential set of strut members. In comparison, a closed cell stent has every curved section of every circumferential set of strut members, except at the distal and proximal ends of the stent, attached to a longitudinal connecting link. A strut member whose curved section is not attached to a longitudinal connecting link is defined as an unconnected strut member.
There are several “open cell” stents that are currently being marketed for the treatment of coronary stenoses. Examples of these are the Tetra stent from Guidant Corporation and the S670 stent from Medtronics, Inc. Each of these stents has a limited number of straight longitudinal connecting links to join adjacent curved sections of adjacent circumferential sets of strut members. These straight longitudinal connecting links can cause outward flaring of the end circumferential sets of strut members as the stent bends around a curve. The interior unconnected strut members also can flare outward when the pre-deployed stent mounted on a balloon is advanced through a curved vessel such as a coronary artery. Any strut that flares outward can engage the vessel wall during stent delivery in a curved vessel thereby preventing the stent from reaching the site that is to be stented.
Most current open cell stents use a multiplicity of circumferential sets of strut members connected by straight longitudinal connecting links. The circumferential sets of strut members are typically formed from a series of diagonal sections connected to curved sections forming a closed-ring, zig-zag structure. This structure opens up as the stent expands to form the element in the stent that provides structural support for the arterial wall. A single strut member is defined as a diagonal section connected to a curved section within one of the circumferential sets of strut members. In current open cell stent designs such as the Tristar stent (Guidant Corp.) these sets of strut members are formed from a single piece of metal having a uniform wall thickness and uniform strut width. Although a stent with uniform width of the strut members will function, if the width is increased to add strength or radiopacity, the sets of strut members will experience increased strain upon expansion. High strain can cause cracking of the metal and potential fatigue failure of the stent under the cyclic stress of a beating heart.
Existing highly radiopaque stents such as the Crossflex coil stent (made from 0.005 inch diameter tantalum wire) by Cordis Corp. and the gold plated NIROYAL stent made by the Boston Scientific Co. can obscure the inside of the vessel because of the high radiopacity over the entire length of the stent. The Be stent of Medtronics, Inc., has small gold markers at the ends of the stent but those markers only mark an end point without allowing visualization of the entire end set of strut members. Fischell et al in U.S. Pat. No. 6,086,604 teaches a closed cell stent with the end sets of strut members being gold plated. Such a stent would have ideal radiopacity but could (like the Be stent) exhibit corrosion due to dissimilar metals placed in an electrolytic solution such as the blood. There has also been significant evidence that gold is a poor surface material for stents because it can increase the risk of subacute thrombosis and restenosis.
Fischell et al in U.S. Pat. No. 5,697,971 show in FIG. 7 a stainless steel stent with increased width diagonal sections in all the circumferential sets of strut members. The U.S. Pat. No. 5,697,971 patent does not teach the use of a variable width for diagonal sections as a means to tailor the stent radiopacity. The U.S. Pat. No. 5,697,971 patent also does not teach specific metals and alloys having greater radiopacity than stainless steel, nor does it teach the use of the alternating curved sections and diagonal sections to form the circumferential sets of strut members. Furthermore, the U.S. Pat. No. 5,697,971 does not teach the use of variable width of curved sections that can provide additional radial rigidity and/or variable width diagonal sections to create relatively greater radiopacity for the end set of strut members.
The present invention is an open cell stent that is designed to optimize many of the operating parameters that are expected for stents in the first decade of the 21st century. Specifically, an optimum stent design would have the following characteristics:
Although many desirable attributes are required of the catheter that is used to deliver the stent, the scope of the present invention is limited to the design of the stent itself However, it should be understood that the reduced foreshortening of this stent is a result of having undulating longitudinal connecting links that readily extend in their longitudinal length when the balloon onto which the stent is crimped is inflated.
To accomplish the goals listed in I. and II. above, the stent would optimally have at least two open cells around the circumference of the stent. A unique feature of the present invention is that each of the strut members whose curved sections are unconnected has a shorter longitudinal length as compared to the longitudinal length of the strut members that are connected by a longitudinal connecting link. This shorter length (optimally on the order of at least 0.1 mm shorter) reduces outward flaring of the unconnected strut members when the stent is advanced through highly curved vessels such as some coronary arteries. Flaring (which is sometimes called “fish-scaling”) can cause the stent to engage the vessel wall as the stent is advanced through curved arteries thus precluding delivery of the stent to its intended location.
Another novel feature of this stent is that the longitudinal connecting links can have an undulating shape so that they can easily expand or contract in their longitudinal length when the stent is advanced through a curved vessel. The extraordinary capability of this stent to bend easily is a combination of the fact that those curved sections of adjacent circumferential sets of strut members that are connected are connected with flexible longitudinal connecting links, and many (typically one-half) of the curved sections are unconnected. Of course, the weakest possible connection that provides the highest degree of longitudinal flexibility is being unconnected. Therefore, the combination of no connections plus the few required connections between the circumferential sets of strut members being by means of highly flexible undulating longitudinal connecting links imparts to this stent an extraordinarily high degree of longitudinal flexibility.
It should also be understood that all the strut members at each end of the stent should also have a shortened longitudinal length because the outside curved section of the end circumferential sets of strut members cannot be connected to any adjacent circumferential set of strut members. By shortening all the end strut members, end flaring of the stent as it is advanced through curved vessels can be reduced. Furthermore, the fact that the interior curved sections of each strut member at the ends of the stent either have no connection or a flexible, undulating longitudinal connecting link connection to an inner strut members is desirable in preventing flaring out of the strut members at the ends of the stent. This is not the case for strut members that have a straight connection to an end circumferential strut such as shown in FIG. 5 of U.S. Pat. No. 5,759,192.
Good radiopacity for the stent is achieved by having a stainless steel stent that has a wall thickness that is the least 0.0045 inches. Another means would be to use a metal with a higher density such as tantalum with a thickness greater than 0.002 inches. A third means for obtaining improved radiopacity would be to sandwich a high density metal between two layers of stainless steel with each of the co-axial tubes having a wall thickness between 0.001 and 0.002 inches.
Another feature of the present invention is that the undulating longitudinal connecting links readily extend in the longitudinal direction when the balloon is inflated. Since the circumferential sets of strut members upon deployment tend to decrease in their longitudinal length, the longitudinal lengthening of the undulating longitudinal connecting links has the effect of minimizing the foreshortening of the deployed stent.
To optimize radiopacity, the ideal radiopaque, open cell stent would have end sets of strut members that are highly radiopaque so that they can be readily seen even using low power fluoroscopy with an interior section of the stent that is visible but not too bright so as to obscure the lumen when high power cine film angiograms are taken. The stent should also have only one material on its outside surface to avoid potential corrosion and that material should not promote subacute thrombosis or restenosis.
The present invention is an open cell stent stent that is designed to have optimal strength and radiopacity with good biocompatibility. Unfortunately, the choices of appropriate biocompatible metals available as thin wall tubing for stent construction are somewhat limited. To achieve optimal radiopacity, the stent design of the present invention is adjusted to the specific radiopacity and strength characteristics of the metal from which the stent is fabricated. What is more, coatings such as parylene may be needed to avoid corrosion from stents with less biocompatible materials and/or dissimilar metals on the stent's exterior surface. Of extreme importance to the present invention is the achievement of optimal radiopacity in a stent that is only 0.004 inches wall thickness or less. Such a stent would have a pre-deployment outer diameter (profile) that would be at least 0.003 inches less than the open cell Tristar stent (Guidant Corp.) that has a wall thickness of 0.0055 inches. Ideally, the stent described herein would have a wall thickness between 0.0025 inches and 0.004 inches.
Described below are the novel design elements for open cell stents formed from stainless steel or a highly radiopaque metal such as tantalum, or plated with highly radiopaque materials like gold.
1. Tapered Strut Width for Stents Formed from Highly Radiopaque Metals
2. End Sets of Strut Members with Thinner Curved Sections
3. Good Sidebranch Access while Maintaining Small Cell Size
4. Flexible Undulating Longitudinal Links with Good Support Between Adjacent Sets of Strut Members
5. Variable Thickness Radiopaque Coatings
6. Polymer Coatings for Stents Coated with Gold or Having Dissimilar Metal Surfaces
7. Attachment of a Drug Coating
8. Providing a Variable Wall Thickness
It is also envisioned that any of the above optimal radiopacity stent designs may be used with plastic coatings such as parylene, antithrombogenic coatings such as heparin or phosphorylcholine or anti-proliferative coatings such as Taxol or Rapamycin, or any other drug as listed above.
Thus an object of the present invention is to have increased longitudinal flexibility for the stent by having some curved sections of each circumferential set of strut members being unconnected to the curved sections of the adjacent circumferential set of strut members with the other curved sections being connected by highly flexible, undulating longitudinal connecting links.
Another object of the present invention is to prevent flaring of the unconnected strut members by having a shorter longitudinal length for the unconnected strut members.
Still another object of the invention is to have generally shorter longitudinal lengths for all the strut members in the circumferential sets of strut members at the stent ends to reduce the tendency for end flaring of the stent.
Still another object of the invention is to decrease the propensity of the stent to have end flaring by having each curved section of the end set of strut members either being unconnected to the curved section of the adjacent (interior) set of strut members or being connected by a highly flexible undulating longitudinal connecting link.
Still another object of the invention is to connect the flexible longitudinal connecting links to the curved sections of the sets of strut members at a point that is close to the line where the diagonal sections join the curved sections, thus further reducing the propensity for end flaring.
Still another object of the invention is to have flexible longitudinal connecting links that are adapted to readily increase their longitudinal length when the balloon is inflated; thus minimizing the extent of stent foreshortening upon stent deployment.
Still another object of the present invention to have a stent that has sets of circumferential strut members with tapered curved sections, the center of the curved sections being wider than the ends of the curved sections so as to reduce plastic strain as the stent is expanded as compared to a curved section with uniform width.
Still another object of the present invention is to have a stent with tapered diagonal sections in the sets of strut members where the center of the diagonal section is narrower than the ends of the diagonal section to reduce the radiopacity of interior sets of strut members of the stent as compared to a stent with diagonal sections having a uniform width.
Still another object of the invention is to have a stent with decreased wall thickness of the interior set of strut members as compared to the end set of strut members so as to have a comparatively higher radiopacity for the end sets of strut members.
Still another object of the present invention is to have a stent having end sets of strut members with tapered diagonal sections that are wider at their center compared to their ends to increase the radiopacity of the end sets of strut members.
Still another object of the present invention is to have end sets of strut members having both shorter diagonal sections and thinner width curved sections as compared to those sections in the interior sets of strut members.
Still another object of the present invention is to have a tantalum stent with wall thickness less than 0.035 inches having tapered sets of strut members whereby the diagonal sections of the interior sets of strut members are less wide than the width at the center of the curved sections.
Still another object of the present invention is to have an open cell stent design with maximum post-deployment interior cell perimeter length that is equal to or greater than 9 mm.
Still another object of the present invention is to have a stent with a radiopaque metal coating where the radiopaque metal coating has greater wall thickness on the end sets of strut members as compared to thickness of the radiopaque metal coating on the interior sets of strut members.
Still another object of the present invention is to have an open cell stent design with “S” or “N” or inverted “N” or other shaped flexible undulating longitudinal connecting links wherein the circumferential extent of each flexible undulating longitudinal connecting link is approximately equal on each side of a line drawn between the proximal and distal attachment points of the flexible undulating longitudinal connecting link.
Still another object of the present invention is to have the stent with optimized radiopacity formed with an outer surface that is plastic coated to improve biocompatibility.
Still another object of the present invention is to have the stent with optimized radiopacity that is coated with a plastic material and an additional material to prevent thrombus formation and/or restenosis; the additional material being selected from the group that includes Rapamycin, Alkeran, Cytoxan, Leukeran, Cis-platinum, BiCNU, Adriamycin, Doxorubicin, Cerubidine, Idamycin, Mithracin, Mutamycin, Fluorouracil, Methotrexate, Thoguanine, Toxotere, Taxol, Etoposide, Vincristine, Irinotecan, Hycamptin, Matulane, Vumon, Hexalin, Hydroxyurea, Gemzar, Oncovin and Etophophos.
Still another object of the present invention is to have a stent coated with a plastic material that includes a radiopaque filler material.
These and other objects and advantages of this invention will become obvious to a person of ordinary skill in this art upon reading the detailed description of this invention including the associated drawings as presented herein.
Although stents are in fact thin-walled, lace-like, cylindrical tubes, they are best illustrated in the form of a flat, two-dimensional layout view as shown in
The pre-deployed stent 10 of the present invention is shown in
Each of the connected curved sections 11 is joined to an adjacent curved section 11 or 11E in the adjacent set of strut members by means of a longitudinally extending, flexible longitudinal connecting link 18 that consists of a interior segment 13, a bottom curved segment 14 and a top curved segment 15. The bottom curved segment 14 is fixedly joined to a connected curved section 11 along the junction line 16. The top curved segment is joined to a connected curved section 11 along the junction line 17. The optimal placement of the junction lines 16 and 17 is at or near the connecting line 22 that joins a curved section 11 (or 11E) to a diagonal section 19L, 19M or 19E. Although an “S” type flexible strut 18 is shown in
As previously stated, the unconnected diagonal sections 19S and 19M have a decreased longitudinal extent as compared to the longitudinal extent of the connected diagonal sections 19L. This design provides an open area so that the bottom curved segments 14 of the flexible longitudinal connecting links 18 do not interfere with the top curved segments 15 when the stent 10 is crimped onto a balloon of a stent delivery system. Thus a decreased profile (i.e.; smaller outer diameter) can be achieved for the pre-deployed stent 10 without causing the bottom curved segment 14 to be placed over (or beneath) the top curved segment 15.
Connected curved sections 11 do not have a tendency to flare outward when the pre-deployed stent 10 is advanced through a curved vessel because the longitudinal connecting struts 18 exert an inward radial force that tends to prevent such flaring. Therefore, one can have connected strut members 24L that are comparatively long and still they will not flare out to engage the vessel wall when the stent 10 is advanced through a curved vessel. However, without longitudinal connecting links, an unconnected curved section (such as the unconnected curved section 12) will tend to flare outward as the stent 10 is advanced around a bend in a curved vessel. To minimize such tendency to flare, the unconnected strut members 24S have a short diagonal section 19S with a reduced longitudinal length L2 as compared to the longitudinal length L1 of the diagonal section 19L of the connected strut members 24L. The unconnected medium strut member 24MU has a diagonal section 19M that has a reduced length as compared to the diagonal 19L of the long strut member 24L. A reduced length is defined herein as being at least 0.1 mm shorter than the length L1 of the long diagonal 19L. By this design, the pre-deployed stent 10 will have little or no flaring or fish-scaling for all interior curved sections of the stent 10. However, there will always be some tendency to have end flaring for each of the end curved sections 12EE of the end set of strut members 30. Reduced flaring of the end curved sections 12EE is accomplished by having comparatively short diagonal sections 19E and also by the location of the attachment line 22 where the links 18 are joined to the curved sections 11E of the end set of strut members 30. The advantageous design of the stent 10 of
Returning now to a discussion of
Another factor in decreasing end flaring (as seen in
Although the greatest longitudinal flexibility for the stent 10 is obtained by connecting some of adjacent sets of strut members with flexible longitudinal connecting links (like the link 18), it should be understood that short, straight links could be used to connect adjacent curved sections such as 12 and 12E. This design concept is shown in
The width of all the curved and diagonal sections of the end circumferential sets of strut members 82 is shown in
It can be clearly seen in
For both the stents 80 and 90, it should be noted that the longitudinal lengths of the interior circumferential sets of strut members 81 and 91 are longer than the longitudinal lengths of the end circumferential sets of strut members 82 and 92. This condition provides for greater radial rigidity for the end set of strut members 82 and 92 and decreases the propensity of the stent 80 or 90 to have outward flaring (fish-scaling) of the end strut members. This is highly desirable to avoid the stent engaging the arterial wall as it is advanced through curved blood vessels.
Various other modifications, adaptations and alternative designs are of course possible in light of the teachings as presented herein. Therefore it should be understood that, while still remaining within the scope and meaning of the appended claims, this invention could be practiced in a manner other than that which is specifically described herein.
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|International Classification||A61F2/06, A61F2/90|
|Cooperative Classification||A61F2002/91541, A61F2002/91516, A61F2002/91525, A61F2/91, A61F2002/91558, A61F2002/91508, A61F2002/91533, A61F2/915, A61F2002/91583, A61F2002/91575|
|European Classification||A61F2/91, A61F2/915|
|May 24, 2004||AS||Assignment|
Owner name: CORDIS CORPORATION, FLORIDA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:FISCHELL, ROBERT E.;FISHCELL, DAVID R.;FISCHELL, TIM A.;REEL/FRAME:015359/0213;SIGNING DATES FROM 20040511 TO 20040513
|Jul 1, 2010||FPAY||Fee payment|
Year of fee payment: 4
|Jul 2, 2014||FPAY||Fee payment|
Year of fee payment: 8
|Mar 31, 2017||AS||Assignment|
Owner name: CARDINAL HEALTH SWITZERLAND 515 GMBH, SWITZERLAND
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:CORDIS CORPORATION;REEL/FRAME:042126/0259
Effective date: 20170329